Droplet collision substance mixing apparatus and droplet collision substance mixing method

ABSTRACT

Provided is a substance mixing apparatus including two or more flow paths in which orifices, from which a fluid that flows therethrough is externally discharged, are formed, oscillation devices that form droplets of the fluid discharged from each of the orifices by oscillating at least the orifice part of the flow paths at a predetermined oscillation frequency and discharge the droplets, and means for causing the droplets discharged from the orifices of the flow paths to collide with one another.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a Continuation Application of U.S. patentapplication Ser. No. 13/377,230 filed on Dec. 9, 2011 which is anational stage of International Application No. PCT/JP2010/003594 filedon May 28, 2010 and claims priority to Japanese Patent Application No.2009-143081 filed on Jun. 16, 2009, the disclosures of which areincorporated herein by reference.

BACKGROUND

The present invention relates to a substance mixing apparatus and asubstance mixing method, more specifically, to an apparatus and methodfor mixing substances by causing droplets discharged from orifices oftwo or more flow paths to collide with one another.

In recent years, in fields of biotechnology and chemistry, an increasein scale and speed of a reaction analysis process is progressing. Forrealizing a high throughput of the reaction analysis process, it iseffective to simultaneously analyze a large number of micro reactionsystems. With a large amount of reaction systems, when carrying out ananalysis on a substance having an extremely high reaction speed, forexample, a reaction progresses in a part of the reaction systems beforemixing of all the reaction systems is ended. As a result, a large numberof reaction systems cannot be analyzed under the same condition, and anaccurate analysis result cannot be obtained.

On the other hand, with micro reaction systems, there is a problem thatit becomes difficult to uniformly mix substances in a certain amount.When the amounts of substances vary among the reaction systems orsubstances are mixed without uniformity, reproducibility of the analysisis lowered, and a reliable analysis result cannot be obtained.

As a technique that enables trace substances to be mixed uniformly in acertain amount, Patent Document 1 discloses a uniformly mixing methodand a uniformly mixing device for a substance that are characterized byincluding two or more piezoelectric type fluid droplet discharge means,and in that small fluid droplets discharged from the fluid dropletdischarge means are caused to collide with one another to be uniformlymixed. According to this technique, a mixing-reaction operation of aminute amount of substances becomes possible, and the substances can becaused to react uniformly so that a uniform reactant can be obtained. Itshould be noted that the “piezoelectric type fluid droplet dischargemeans” adopted in the uniformly mixing method for a substance and thelike is a fluid droplet discharge apparatus that generates a pressure ina fluid compression chamber by deforming a partial wall portion of thefluid compression chamber by a piezoelectric/electrostrictive device tothus inject a fluid in the fluid compression chamber from a nozzle hole.

-   Patent Document 1: Japanese Patent Application Laid-open No. Hei    11-262644

DISCLOSURE OF THE INVENTION Problems to be Solved by the Invention

Conventionally, in the fields of biotechnology and chemistry,biologically-relevant minute particles such as a cell, a microorganism,and a liposome, and synthetic minute particles such as latex particles,gel particles, and industrial particles have been mixed with variouscompounds, and a reaction of the minute particles and the compounds hasbeen analyzed.

As an example, in the field of biotechnology, lymphocytes and antigensare mixed in a large number of wells to screen antigen-specific B cellscoupled with the antigens, or lymphocytes are mixed with cancer cells orvirus-infected cells in the wells to screen cellular disorder T cellsthat have caused a destruction of the cancer cells and the like. Thedetected antigen-specific B cells and cellular disorder T cells aresubjected to a gene analysis after retrieval and used in developments ofantibody drugs and cell immunity treatments. In the screenings,lymphocytes are dispensed singly or plurally to the wells to be mixedwith antigens and the like, and a high throughput screening called“single-cell screening” for detecting a reaction and an object cell iscarried out.

In the uniformly mixing method and mixing apparatus for a substancedisclosed in Patent Document 1 above, although a certain amount of tracesubstances can be mixed uniformly, mixing of such minute particles witha substance and mixing of minute particles with minute particles are notassumed.

In this regard, the present invention mainly aims at providing asubstance mixing apparatus that is capable of uniformly mixing tracesubstances in a certain amount and also mixing minute particles.

Means for Solving the Problems

For solving the problems above, according to the present invention,there is provided a substance mixing apparatus including: two or moreflow paths in each of which an orifice, from which a fluid that flowstherethrough is externally discharged, is formed; an oscillation devicethat forms droplets of the fluid discharged from each of the orifices byoscillating at least the orifice part of the flow paths at apredetermined oscillation frequency and discharges the droplets; andmeans for causing the droplets discharged from the orifices of the flowpaths to collide with one another.

The substance mixing apparatus further includes: a detection means fordetecting minute particles included in the fluid that flows through theflow paths; and a control means for calculating a flow sending intervalof the minute particles based on a detection signal of the minuteparticles from the detection means and controlling the oscillationfrequency of the oscillation device based on the calculated flow sendinginterval. The control means controls the oscillation frequency such thata predetermined number of minute particles are incorporated in thedroplets discharged from the orifices of the flow paths through whichthe fluid including the minute particles flows.

Moreover, the substance mixing apparatus further includes: a chargemeans for imparting a charge to the droplets discharged from theorifices; and paired electrodes provided oppositely along a movementdirection of the droplet obtained by the collision. The movementdirection of the droplet obtained by the collision is controlled by anelectric action force generated by the charge imparted to the dropletsdischarged from the orifices and the paired electrodes. By controllingthe movement direction of the droplet obtained by the collision, thedroplets can be retrieved in two or more areas.

Alternatively, the substance mixing apparatus may further include adrive means for relatively moving the orifices of the flow paths withrespect to two or more areas for retrieving and accommodating thedroplet obtained by the collision. By relatively moving the orifices ofthe flow paths with respect to the areas, the droplet obtained by thecollision can be retrieved in the two or more areas.

In the substance mixing apparatus, it is favorable for the flow paths tobe formed on a single microchip. The present invention also provides amicrochip including two or more flow paths in each of which an orifice,from which a fluid that flows therethrough is externally discharged, isformed and that form droplets of the fluid discharged from each of theorifices by an oscillation of at least the orifice part and dischargethe droplets, the flow paths being provided, such that the dropletsdischarged from the orifices collide with one another.

In the microchip, a predetermined part of the flow paths is structuredas a detection portion for detecting minute particles included in thefluid that flows through the flow paths, and a cross-sectional area ofthe orifice part of the flow paths is smaller than that of the detectionportion.

In the microchip, a minute pipe that introduces a laminar flow of asecond fluid including minute particles in a laminar flow of a firstfluid that flows through the flow paths may be provided upstream fromthe detection portion in a fluid feeding direction.

It is favorable for the minute pipe to be formed of metal to which avoltage can be applied. Accordingly, the minute pipe can be structuredas a charge means for imparting a charge to the droplets discharged fromthe orifices.

The microchip may further include an oscillation device that oscillatesat least the orifice part or the flow paths.

Further, the present invention provides a substance mixing methodincluding: arranging two or more flow paths in each of which an orifice,from which a fluid that flows therethrough is externally discharged, isformed; forming droplets of the fluid discharged from the orifices byoscillating at least the orifice part of the flow paths at apredetermined oscillation frequency and discharging the droplets; andcausing the droplets discharged from the orifices of the flow paths tocollide with one another.

In the substance mixing method, a fluid including minute particles maybe caused to flow through either one of the flow paths, and the dropletsthat include the minute particles and are discharged from the orifice ofthe flow path may be caused to collide with the droplets discharged fromthe orifice of the other flow path, to thus mix the minute particleswith a substance. In this case, by controlling the oscillation frequencybased on a flow sending interval of the minute particles included in thefluid that flows through the flow paths, a predetermined number ofminute particles can be incorporated in the droplets discharged from theorifices of the flow paths.

The substance mixing method may further include: imparting a charge tothe droplets discharged from the orifices; controlling a movementdirection of the droplet obtained by the collision by an electric actionforce generated by paired electrodes provided oppositely along themovement direction of the droplet obtained by the collision and thecharge imparted to the droplets; and dispensing the droplet obtained bythe collision to two or more areas. Alternatively, the droplet obtainedby the collision may be dispensed to two or more areas by relativelymoving the orifices of the flow paths with respect to the areas.

In the substance mixing method, it is favorable for the flow paths to beformed on a single microchip.

In the present invention, the “minute particles” widely includebiologically-relevant minute particles such as a cell, a microorganism,and a liposome, and synthetic minute particles such as latex particles,gel particles, and industrial particles.

The biologically-relevant minute particles include chromosomesconstituting various cells, liposomes, mitochondria, and organelle (cellorganelle). Target cells include animal cells (hemocyte cells) and plantcells. The microorganisms include bacterium such as Bacillus coli,viruses such as a tobacco mosaic virus, and fungi such as a yeast. Thebiologically-relevant minute particles may also includebiologically-relevant polymers such as a nucleic acid, a protein, and acomplex of those. Moreover, the industrial particles may be, forexample, an organic or inorganic polymer material or metal. The organicpolymer material includes polystyrene, styrene-divinylbenzen, andpolymethylmethacrylate. The inorganic polymer material includes glass,silica, and a magnetic material. The metal includes a gold colloid andaluminum. The shape of the minute particles is normally a sphere, butmay instead be a nonspherical shape, and the size and mass are also notparticularly limited.

SUMMARY

According to the present invention, a substance mixing apparatus that iscapable of uniformly mixing trace substances in a certain amount andalso mixing minute particles can be provided.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 A diagram for explaining a first embodiment of a substance mixingapparatus according to the present invention.

FIG. 2 A diagram for explaining a modified example 5 of the firstembodiment of the substance mixing apparatus according to the presentinvention.

FIG. 3 A diagram for explaining a second embodiment of the substancemixing apparatus according to the present invention.

FIG. 4 A diagram for explaining a modified example of the secondembodiment of the substance mixing apparatus according to the presentinvention.

FIG. 5 A diagram for explaining a detection means and a control meansequipped in the substance mixing apparatus according to the presentinvention.

FIG. 6 A diagram for explaining a structure for dispensing mixeddroplets in the substance mixing apparatus according to the firstembodiment.

FIG. 7 A diagram for explaining the structure for dispensing mixeddroplets in the substance mixing apparatus according to the modifiedexample of the first embodiment.

FIG. 8 A diagram for explaining a third embodiment of the substancemixing apparatus according to the present invention.

FIG. 9 A diagram for explaining a microchip according to the presentinvention.

FIG. 10 A diagram schematically showing droplets discharged from themicrochip according to the present invention.

FIG. 11 Diagrams for explaining a setting position of a minute pipe 116,a structure of a flow path 11 in the vicinity of a narrowing portion117, and states of a flowing sample fluid laminar flow and sheath fluidlaminar flow.

FIG. 12 Diagrams for explaining structures of a pressor portion 118 andthe flow path 11 in the vicinity of an orifice 111, and states of theflowing sample fluid laminar flow and sheath fluid laminar flow.

FIG. 13 Diagrams for explaining a width and depth of the flow path 11 atrespective portions.

FIG. 14 Diagrams for explaining other favorable embodiments on the widthand depth of the flow path 11.

FIG. 15 A diagram for explaining a structure for dispensing mixeddroplets in a microchip-type substance mixing apparatus.

BEST MODES FOR CARRYING OUT THE INVENTION

Hereinafter, favorable embodiments for embodying the present inventionwill be described with reference to the drawings. It should be notedthat the embodiments described below are mere examples of representativeembodiments of the present invention, and the range of the presentinvention should not be interpreted narrowly with this. It should benoted that descriptions will be given in the following order.

1. Collision Means

(1-1) First Embodiment

(1-2) Second Embodiment

2. Detection Means and Control Means

3. Dispense of Mixed Droplets

(3-1) Dispense by Charge Means

(3-2) Dispense by Drive Means

4. Microchip-Type Substance Mixing Apparatus

(4-1) General Overview of Apparatus Structure

(4-2) Microchip

(4-3) Dispense by Charge Means

(4-4) Dispense by Drive Means

1. Collision Means (1-1) First Embodiment

FIG. 1 is a schematic diagram for explaining a first embodiment of asubstance mixing apparatus according to the present invention. Thesubstance mixing apparatus of this embodiment has characteristics thatsubstances are mixed by causing droplets discharged from orifices of twoflow paths to collide with one another. The figure shows a structure ofmeans equipped in the substance mixing apparatus for causing droplets tocollide with one another.

In the figure, the reference numerals 11 and 12 denote flow pathsthrough which fluids including substances to be mixed flow. In the flowpaths 11 and 12, orifices 111 and 121 for externally discharging theflowing fluids are formed. Further, the reference numerals 112 and 122denote oscillation devices that oscillate at least the orifice 111, 121part of the flow paths 11 and 12 at a predetermined oscillationfrequency to thus form droplets of the fluids to be discharged from theorifices 111 and 121 and discharge them. The oscillation devices 112 and122 are each constituted of a piezo-oscillation device or the like andprovided so as to apply a predetermined oscillation to the entire flowpaths 11 and 12 or a part including at least the orifice 111, 121 part.

The fluids including the substances to be mixed are sent to the flowpaths 11 and 12 by a fluid feeding means (not shown) and discharged asdroplets A and B from the orifices 111 and 121 by the function of theoscillation devices 112 and 122. At this time, by adjusting a fluidfeeding amount (flow rate) with respect to the flow paths 11 and 12,diameters of the orifices 111 and 121, an oscillation frequency of theoscillation devices 112 and 122, and the like, sizes of the droplets Aand B can be adjusted, and substances can be incorporated into thedroplets in a certain amount. The discharged droplets A and B become asingle droplet G by colliding with each other at a predeterminedposition in a space outside the flow paths 11 and 12, and the substancesincluded in the droplets A and B are mixed in the droplet G. The dropletG flies according to an inertia of the droplets A and B and retried in avessel denoted by the reference numeral 2 in the figure. A collisionangle θ₁₂ of the droplets A and B and flying distances L₁₁ and L₁₂ tothe collision position are set as appropriate based on a flying speed orsize of the droplets A and B, a discharge interval from the orifices 111and 121, and the like so as to enable the droplets A and B to collidewith one another.

In the substance mixing apparatus, by discharging the fluids includingthe substances to be mixed from the orifices 111 and 112 of the flowpaths 11 and 12 as the droplets A and B and causing them to collide withone another, the substances included in the droplets can be uniformlymixed in a short time. Moreover, since substances can be incorporatedinto the droplets A and B by a certain amount, variances in the amountof mixed substances are not caused.

The fluid that flows through the flow path 11 or 12 may include 1 or 2or more substances so that the 1 or 2 or more substances included in thedroplet A and the 1 or 2 or more substances included in the droplet Bare mixed in the droplet G by the collision of the droplets A and B.

The collision angle θ₁₂ of the droplets A and B and the distances L₁₁and L₁₂ to the collision position can be set as appropriate based on theflying speed or size of the discharged droplets A and B, the dischargeinterval from the orifices 111 and 121, and the like. For example, asshown in FIG. 2, it is possible to set the flow paths 11 and 12 atalmost 90 degrees so that the collision angle θ₁₂ of the droplets A andB discharged from the orifices of the flow paths becomes almost 90degrees. The collision angle of the droplets can be set as appropriateto be larger than 0 degree and smaller than 180 degrees.

FIG. 2 shows a setting position of the vessel 2 in a case where, sincethe mass of the droplet B is sufficiently smaller than that of thedroplet A, a flying direction of the droplet G after the collision doesnot vary as compared to the discharge direction of the droplet A. Sincethe droplet G flies according to the inertia of the droplets A and B,the vessel 2 needs to be placed in a direction in which the droplet Gflies.

It should be noted that in the first embodiment shown in FIG. 1 and amodified example shown in FIG. 2, all of the droplets A and B do notneed to collide to be mixed, and there may be a droplet A that does notcollide with the droplet B. Moreover, there may be a droplet B that doesnot collide with the droplet A. For example, a droplet B discharged fromthe orifice 121 can be mixed with a droplet A discharged from theorifice 111 at a two-to-one ratio. In this case, the droplet A itselfthat did not collide with the droplet B and the droplet G obtained bycolliding and mixing with the droplet B are retrieved in the vessel 2.The droplet B can be caused to collide with the droplet A at atwo-to-one ratio by adjusting the flying distances L₁₁ and L₁₂ to thecollision position of the droplets A and B, the discharge interval fromthe orifices, and the like.

(1-2) Second Embodiment

FIG. 3 is a schematic diagram for explaining a second embodiment of thesubstance mixing apparatus according to the present invention. Thesubstance mixing apparatus of this embodiment has characteristics that afluid including minute particles is discharged from an orifice of oneflow path and caused to collide with droplets discharged from orificesof other two flow paths to thus mix the substances including minuteparticles. The figure shows a structure of means equipped in thesubstance mixing apparatus for causing the droplets to collide with oneanother.

In the figure, the reference numerals 11, 12, and 13 denote flow pathsthrough which fluids including substances to be mixed flow. Of those, afluid including minute particles P flows through the flow path 11.Orifices 111, 121, and 131 for externally discharging the flowing fluidsare formed in the respective flow paths, and oscillation devices 112,122, and 132 for forming droplets of the fluids to be discharged fromthe orifices and discharging them are provided.

The fluids including the substances to be mixed are sent to the flowpaths by a fluid feeding means (not shown) and discharged as droplets A,B, and C from the orifices by the function of the oscillation devices.Of those, the droplets A discharged from the orifice 111 include theminute particles P included in the fluid that flows through the flowpath 11. The discharged droplets A, B, and C become a single droplet Gby colliding with one another at a predetermined position in a spaceoutside the flow paths 11, 12, and 13, and the minute particles Pincluded in the droplet A are mixed. with substances included in thedroplets B and C in the droplet G. After that, the droplet G fliesaccording to an inertia of the droplets A, B, and C and retried in thevessel 2.

The collision angle θ₁₂ of the droplets A and B, a collision angle θ₁₃of the droplets A and C, and the flying distances L₁₁, L₁₂, and L₁₃ tothe collision positions of the droplets are set as appropriate based ona flying speed or size of the droplets, a discharge interval from theorifices, and the like so as to enable the droplets to collide with oneanother.

In the substance mixing apparatus, the fluid including the minuteparticles P is discharged from the orifice 111 of the flow path 11 as adroplet A, and the fluids including substances to be mixed aredischarged from the orifices 121 and 132 of the flow paths 12 and 13 asdroplets B and C. By causing those droplets to collide with one another,the minute particles and substances included in the droplets can beuniformly mixed within a short time. Moreover, since the substances canbe incorporated into the droplets B and C by a certain amount, aplurality of substances can be mixed with the minute particles P withoutcausing variances in the amounts.

In mixing the droplets A, B, and C, collision and mixing of the threedroplets may be carried out at the same time, or collision and mixing ofany of the two droplets may be carried out first. Collision and mixingof the droplets can be carried out at arbitrary timings. For example, asshown in FIG. 4, the flow paths 11 and 12 are set almost at 90 degreesso that the droplet A that is discharged from the orifice 111 andincludes the minute particles P first collides with the droplet Bdischarged from the orifice 121 to thus obtain a droplet G. Accordingly,the minute particles P and substance included in the droplets A and Bare mixed. Next, the flow path 13 is set almost at 90 degrees withrespect to the flying direction of the droplet G so that the droplet Cdischarged from the orifice 131 collides with the droplet G to thusobtain a droplet H. Accordingly, the minute particles and substanceincluded in the droplets H and C can be mixed.

Further, all of the droplets A, B, and C do not always need to collideand be mixed, and only two of those may collide to be mixed. Thecombination of the droplets to undergo collision and mixing can be setarbitrarily. For example, the droplet B discharged from the orifice 121can be caused to collide with the droplet A discharged from the orifice111 at a two-to-one ratio and be mixed therewith. In this case, thedroplet that collides with the droplet C discharged from the orifice 131is the droplet A itself or the droplet G in which the droplets A and Bare mixed. Then, by selecting a combination of the droplets A and G andthe droplet C discharged from the orifice 131 for collision, a mixtureof the droplets A and C, a mixture of the droplets A, B, and C, or amixture of the droplets A and B can be obtained as the droplet H to beeventually retrieved in the vessel 2. The combination of the dropletsfor collision and mixing can be set arbitrarily by adjusting the flyingdistances L₁₁, L₁₂, L₂₃, and L₁₃ to the collision positions of thedroplets, the flying speeds of the droplets A, B, and C, the dischargeinterval from the orifices, and the like.

Although the cases where the substances are mixed by providing two flowpaths 11 and 12 in FIGS. 1 and 2 and three flow paths 11, 12, and 13 inFIGS. 3 and 4 have been described, the number of flow paths to beprovided is not particular limited in the substance mixing apparatusaccording to the present invention, and 4 or more flow paths may beprovided.

2. Detection Means and Control Means

FIG. 5 is a schematic diagram for explaining a structure forincorporating a predetermined number of minute particles in a droplet tobe discharged from the orifice of the flow path in the substance mixingapparatus according to the present invention.

As described with reference to FIGS. 3 and 4, in the substance mixingapparatus according to the present invention, droplets including minuteparticles are discharged from the orifice of the flow path and caused tocollide with the droplets discharged from the orifice of the other flowpath to thus mix substances including the minute particles. At thistime, the number of minute particles included in a droplet is notparticularly limited and can be set arbitrarily. FIG. 3 has shown theexample where one minute particle P is incorporated in the droplet Adischarged from the orifice 111 of the flow path 11. Moreover, FIG. 4has shown the example where 0 or 1 minute particle P is incorporated inevery other droplet A discharged from the orifice 111 of the flow path11.

The number of minute particles to be incorporated in a droplet can beset to an arbitrary number of 0 or 1 or more by adjusting the fluidfeeding amount (flow rate) with respect to the flow paths, the diameterof the orifices, the oscillation frequency of the oscillation devices,and the like. The number of minute particles to be incorporated in adroplet can be favorably controlled by controlling the oscillationfrequency of the oscillation devices in particular, the details of whichwill be given hereinafter with reference to FIG. 5.

In FIG. 5, the reference numerals 31, 32, and 33 each denote a detectionmeans for detecting the minute particles P included in the fluid thatflows through the flow path 11. The detection means 31, 32, and 33irradiate laser light (measurement light) onto the flowing minuteparticles P at a predetermined part of the flow path 11 and convertdetected light generated from the minute particles P (measurement targetlight) into electric signals.

The detection means 31, 32, and 33 can be constituted of a laser lightsource, an irradiation system 31 (detection means 31) constituted of alaser light source and collecting lens for collecting and irradiatinglaser light onto the minute particles P, a dichroic mirror, a bandpassfilter, and the like, and a detection system 32 (detection means 32)that collects measurement target light generated from the minuteparticles P by the irradiation of the laser light in a detector 33(detection means 33). The detector 33 may be constituted of, forexample, an area image pickup device such as a PMT (Photo MultiplierTube), a CCD, and a CMOS. It should be noted that although theirradiation system and the collecting system are structured separatelyin the figure, the irradiation system and the collecting system may havestructures in which they have a common optical path.

The measurement target light detected by the detector 33 is light thatis generated from the minute particles P by the irradiation of the laserlight, and forward-scattered light or side-scattered light, scatteredlight of Rayleigh scattering, Mie scattering, or the like, andfluorescent light can be used, for example. The measurement target lightis converted into an electric detection signal and output to acontroller 4. The controller 4 calculates the flow sending interval ofthe minute particles P in the flow path 11 based on the detection signaland controls the oscillation frequency of the oscillation device 112based on the calculated flow sending interval.

By oscillating the oscillation device 112 at a predetermined oscillationfrequency based on the flow sending interval of the minute particles Pin the flow path 11, control can be performed to incorporate apredetermined number of minute particles P in the droplet A dischargedfrom the orifice 111. FIG. 5 has shown the example where control isperformed to incorporate one minute particle P in the droplet A. Bycontrolling the oscillation frequency based on the flow sendinginterval, it also becomes possible to incorporate two or more minuteparticles in the droplet or incorporate different numbers of minuteparticles in the droplet, for example.

It should be noted that the detection means 31, 32, and 33 may bereplaced by, for example, an electric or magnetic detection means. Whenelectrically or magnetically detecting minute particles, minuteelectrodes are oppositely provided on both sides of the flow path 11,and a resistance value, a capacitance value, an inductance value, animpedance, and a change value of an electric field between theelectrodes, or a magnetization, a magnetic field change, and the likeare measured.

It should be noted that although FIGS. 3 to 5 have shown the examplewhere the droplets A including the minute particles are discharged fromthe orifice 111 of the flow path 11, the fluid including the minuteparticles may flow through two or more flow paths. For example, it isalso possible to cause a fluid including minute particles to also flowthrough the flow path 12 in addition to the flow path 11 and dischargedroplets A and B including the minute particles from the orifices 111and 121. In this case, by generating the droplet G (see FIG. 3) ordroplet H (see FIG. 4) by causing the droplets A, B, and C to collidewith one another, the minute particles included in the droplets A and Band the substance included in C are mixed. Either of the fluids flowingthrough the flow paths 11 and 12 may include minute particles of onetype or two types or more, or the minute particles may either be thesame or different.

3. Dispense of Mixed Droplets (3-1) Dispense by Charge Means

FIG. 6 is a schematic diagram for explaining a structure for dispensingthe collided/mixed droplet G in the substance mixing apparatus accordingto the first embodiment. The figure shows a structure for dispensing thedroplet. G to a plurality of areas by controlling a movement directionof the droplet G using an electric action force. In the figure, thereference numeral 21 denotes each of the plurality of areas formed inthe vessel 2.

The droplets A and B discharged from the flow paths 11 and 12 collidewith each other to become a droplet G which flies according to an inertof the droplets A and B. In the figure, the reference numerals 51, 51denote first paired electrodes provided oppositely along the movementdirection of the droplet G. Further, the reference numerals 52, 52denote second paired electrodes similarly provided oppositely along themovement direction of the droplet G. The first paired electrodes 51, 51and the second paired electrodes 52, 52 are provided such that oppositeaxes thereof become orthogonal to each other. In other words, the firstpaired electrodes 51, 51 are opposed in the X-axis direction in thefigure, and the second paired electrodes 52, 52 are opposed in theY-axis direction.

On the other hand, in the figure, the reference numerals 113, 113 denotea charge means for charging the droplets A discharged from the flow path11 and imparting a charge. Further, the reference numerals 123, 123denote a charge means for similarly imparting a charge to the droplets Bdischarged from the flow path 12. Here, the case where the charge meansare structured as the paired electrodes provided along the dischargedirection of the droplets A and B has been shown. However, the structureof the charge means is not particularly limited as long as it is capableof imparting a charge to the droplets A and B. As an example of otherstructures of the charge means, there is a structure in which a metalmember is provided so as to come into contact with the fluids flowingthrough the flow paths 11 and 12, and a voltage is imparted to the metalmember.

Either one or both of the droplets A and B discharged from the flowpaths 11 and 12 can be imparted with a positive or negative charge topositively or negatively charge the droplet G obtained after thecollision. Then, by the charge imparted to the droplet G and an electricrepulsion force or absorption force that acts between the first pairedelectrodes 51, 51, the movement direction of the droplet G that passesthe first paired electrodes 51, 51 is controlled in positive andnegative directions along the X axis. Furthermore, by the chargeimparted to the droplet G and an electric force that acts between thesecond paired electrodes 52, 52, the movement direction of the droplet Gthat passes the second. paired electrodes 52, 52 is controlled inpositive and negative directions along the Y axis.

The flying direction of the droplet G that has passed the second pairedelectrodes 52, 52 can be arbitrarily controlled in the X- and Y-axisdirections in the figure by varying a voltage applied to the firstpaired electrodes 51, 51 and the second paired electrodes 52, 52 andadjusting an intensity of the electric action force between the dropletG. Accordingly, the droplet G can be guided to the plurality of areas 21formed in the vessel 2 so that the droplet G is retrieved in the areas.0 or 1 or more droplet G can be guided to and retrieved in each of theareas 21. It should be noted that control of the flying direction of thedroplet G can be adjusted by varying the charge imparted to the dropletA or B by the charge means 113, 113 or 123, 123.

A fluid including minute particles can be caused to flow through theflow paths so that droplets including the minute particles aredischarged from the orifices, and by oscillating the oscillation device112 at a predetermined oscillation frequency based on the flow sendinginterval of the minute particles P in the flow path 11, for example,control can be performed such that a predetermined number of minuteparticles P are incorporated in the droplet A discharged from theorifice 111 (see FIG. 5). In this case, it is also possible toincorporate a predetermined number of minute particles P in the dropletG obtained after the collision of the droplet A and dispense a certainnumber of minute particles to the plurality of areas 21 by guiding thedroplet G to each of the areas 21 formed in the vessel 2 for retrieval.The number of minute particles to be incorporated in the droplet is notparticularly limited and can be set arbitrarily, but by dispensing thedroplets each including one cell as a minute particle one each to theareas, for example, it can be used for pharmacokinetics studies thatuses single-cell screening.

(3-2) Dispense by Drive Means

FIG. 7 is a schematic diagram for explaining a structure for dispensingthe droplet G obtained after the collision and mixing in the substancemixing apparatus according to a modified example of the firstembodiment. The figure shows a structure for dispensing the droplet G tothe plurality of areas 21 of the vessel 2 by moving the flow paths bythe drive means.

Relative positions of the flow paths 11 and 12 with respect to thevessel 2 can be changed in the X- and Y-axis directions in the figure bya drive means (not shown). The drive means is not particularly limitedas long as it can move the relative positions of the flow paths 11 and12 with respect to the vessel 2 and can be constituted of, for example,a feed screw, a guide, and a motor.

By arbitrarily controlling the flying direction of the droplet G in theX- and Y-axis directions in the figure by sequentially varying therelative positions of the flow paths 11 and 12 with respect to thevessel 2 by the drive means, 0 or 1 or more droplet G can be retrievedin each of the plurality of areas 21 formed in the vessel 2. It shouldbe noted that the number of droplets G to be retrieved in the areas 21may all be the same or may be different.

It should be noted that FIGS. 6 and 7 have shown the case where amulti-plate in which 96 wells (areas 21) are formed on a plasticsubstrate is used as the vessel 2. Various plastic vessels that arenormally used may also be used as the vessel 2, and by providing aplurality of those, 0 or 1 or more droplet G can be guided to andretrieved in each of the vessels 2.

4. Microchip-Type Substance Mixing Apparatus (4-1) General Overview ofApparatus Structure

FIG. 8 is a schematic diagram for explaining a third embodiment of thesubstance mixing apparatus according to the present invention. Thesubstance mixing apparatus of this embodiment has characteristics thatthe flow paths through which fluids including substances to be mixedflow are formed on a single microchip. The figure shows a schematicstructure of the apparatus.

In the figure, the reference numeral 1 denotes a microchip. On themicrochip 1, the flow paths 11, 12, and 13 through which fluidsincluding substances to be mixed flow are formed. Of those, a fluidincluding minute particles flows through the flow path 11.

The reference numeral 112 denotes an oscillation device for formingdroplets of the fluids discharged from the orifices of the flow paths11, 12, and 13 and discharging them. Here, an internal structure of thechip in which the oscillation device 112 is integrally formed with themicrochip will be described, but it is also possible for the oscillationdevice 112 to be provided on the apparatus main body side at a positionwhere it comes into contact with the chip when the chip is mounted tothe apparatus.

Further, the reference numerals 31 and 32 denote a detection means fordetecting the minute particles included in the fluid that flows throughthe flow path 11, the detection means being an irradiation system and adetection system (also see FIG. 5).

The fluid including substances to be mixed is fed to the flow paths 11,12, and 13 by a fluid feeding means (not shown) and discharged asdroplets from the orifices of the flow paths by the function of theoscillation device 112. The discharged droplet collides at apredetermined position in a space outside the microchip 1 to become asingle droplet G, with the result that the substances are mixed (alsosee FIG. 3). Further, the movement direction of the droplet G obtainedafter the collision is controlled by the first paired electrodes 51, 51and the second paired electrodes 52, 52 so that the droplet G is guidedto and retrieved in the plurality of areas 21 formed in the vessel 2(also see FIG. 6).

The microchip 1 may be formed of glass or various plastics (PP, PC, COP,PDMS, etc.). It is desirable for the material of the microchip to havepermeability with respect to laser light irradiated by the detectionmeans 31 and have less optical errors due to small autogenousfluorescence and a small wavelength. dispersion.

The formation of the flow path 11 and the like on the microchip 1 can becarried out by wet etching or dry etching of a glass substrate, ornanoimprint, injection molding, and mechanical processing of a plasticsubstrate. The microchip 1 can be formed by sealing a substrate on whichthe flow path 11 and the like are formed with a substrate formed of thesame material or a different material.

(4-2) Microchip

Referring to FIG. 9, the structure of the microchip 1 will be describedin detail.

On the microchip 1, a sample fluid inlet 115 into which a fluidincluding minute particles to be mixed (hereinafter, referred to as“sample fluid”) is introduced and a sheath fluid inlet 114 into which asheath fluid is introduced are formed. The sample fluid introduced intothe sample fluid inlet 115 flows through a minute pipe 116 to be fed tothe flow path 11. Further, the sheath fluid introduced into the sheathfluid inlet 114 first splits bidrectionally in the positive and negativedirections on the Y axis from the sheath fluid inlet 114 to be fed, andthen turns twice at almost 90 degrees to join at the position where theminute pipe 116 is provided.

The minute pipe 116 introduces the sample fluid that has been introducedfrom the sample fluid inlet 115 into a sheath fluid laminar flow flowingthrough the flow path 11 after the confluence. Accordingly, the minutepipe 116 feeds the sample fluid downstream of the flow path 11 while thesample fluid laminar flow is surrounded by the sheath fluid laminarflow. By feeding the sample fluid laminar flow to the center of thesheath fluid laminar flow, minute particles in the sample fluid laminarflow can be fed while being aligned in one line in the flow path 11.

The detection means (indicating only irradiation system 31 in figure)irradiates laser light onto the minute particles flowing through theflow path 11 an a line, detects measurement target light generated fromthe minute particles, and converts it into an electric detection signal.Hereinafter, a part where the detection of minute particles is carriedout in the flow path 11 will be referred to as “detection portion”(denoted by symbol F in figure). The sample fluid and sheath fluid thathave passed the detection portion F are discharged outside the flow path11 from the orifice 111 opened at one side of the microchip 1.

The detection signal from the detection means is output to thecontroller 4 (not shown) which calculates the flow sending interval ofthe minute particles in the flow path 11 based on the detection signaland controls the oscillation frequency of the oscillation device 112based on the calculated flow sending interval (also see FIG. 5). Then,by oscillating the microchip 1 at a predetermined oscillation frequencybased on the flow sending interval of the minute particles, theoscillation device 112 forms droplets of the sample fluid and sheathfluid discharged from the orifice 111 and controls to incorporate apredetermined number of minute particles in the droplets. FIG. 10 showsa case where control is performed to incorporate one minute particle Pin the droplet A discharged from the orifice 111. It is also possible toincorporate two or more minute particles in each droplet or incorporatedifferent numbers of minute particles in the droplets.

It should be noted that the detection means may be replaced by, forexample, an electric or magnetic detection means as already describedabove. When electrically or magnetically detecting minute particles,minute electrodes are oppositely provided on both sides of the flow path11, and a resistance value, a capacitance value, an inductance value, animpedance, and a change value of an electric field between theelectrodes, or a magnetization, a magnetic field change, and the likeare measured.

Moreover, on the microchip 1, inlets 124 and 134 into which fluidsincluding substances to be mixed are introduced are formed. The fluidsintroduced into the flow paths 12 and 13 via the inlets 124 and 134 arealso discharged as droplets B and C from the orifices 121 and 131 by theoscillation of the oscillation device 112.

The orifice 111 of the flow path 11, the orifice 121 of the flow path12, and the orifice 131 of the flow path 131 are opened on the same sideof the microchip 1 and provided such that the droplets A, B, and Cdischarged from the orifices of the flow paths can collide with oneanother. Specifically, as described with reference to FIG. 3, thecollision angle θ₁₂ of the droplets A and B, the collision angle θ₁₃ ofthe droplets A and C, and the flying distances L₁₁, L₁₂, and L₁₃ to thecollision positions of the droplets are set as appropriate based on theflying speed and size of the droplets, the discharge interval from theorifices, and the like to enable the droplets to collide with oneanother.

In the substance mixing apparatus, the fluid including the minuteparticles P is discharged as the droplets A from the orifice 111 of theflow path 11 and the fluids including substances to be mixed aredischarged as the droplets B and C from the orifices 121 and 131 of theflow paths 12 and 13. By causing those droplets to collide with oneanother, the minute particles and substances included in the dropletscan be uniformly mixed within a short time.

Further, in the substance mixing apparatus, by adjusting the fluidfeeding amount (flow rate) with respect to the flow paths 12 and 13, thediameters of the orifices 121 and 131, and the like, the sizes of thedroplets A, B, and C can be adjusted and the substances can beincorporated into the droplets in a certain amount. Therefore, theplurality of substances can be mixed with the minute particles P withoutcausing variances in the amounts.

Furthermore, in the substance mixing apparatus, since the flow paths 11,12, and 13 are formed on a single microchip 1, positioning (alignment)of the flow paths and the orifices to enable the droplets to collidewith one another do not need to be carried out. Moreover, by using aninexpensive microchip that can be used disposably as means for formingdroplets and means for causing the droplets to collide with one another,it becomes possible to prevent contamination from occurring amonganalysis samples.

FIGS. 9 and 10 have shown the case where substances are mixed byproviding three flow paths 11, 12, and 13. However, the number of flowpaths to be provided in the microchip 1 is not particularly limited andmay be 4 or more. Moreover, the collision angle θ₁₂ of the droplets Aand B, the collision angle θ₁ of the droplets A and C, and the flyingdistances L₁₁, L₁₂ and L₁₃ to the collision positions of the dropletscan be set arbitrarily within the range in which the droplets arecapable of colliding with one another, and along with that, the settingpositions of the flow paths 11, 12, and 13 and orifices 111, 121, and131, and the like on the microchip 1 can be changed as appropriate.

Furthermore, although FIGS. 9 and 10 have shown the example of a casewere the droplets A including minute particles are discharged from theorifice 111 of the flow path 11, the fluid including minute particlesmay be caused to flow through two or more flow paths. For example, it isalso possible to provide the sheath fluid inlet, the minute pipe, thedetection portion F, and the like in the flow path 12 as in the flowpath 11 and discharge the droplets A and B including the minuteparticles from the orifices 111 and 121. In this case, both of thefluids flowing through the flow paths 11 and 12 may include one type ortwo or more types of minute particles, and the minute particles includedin the fluids may either be the same or different.

Hereinafter, with reference to FIGS. 11 to 14 in addition to FIG. 9, thestructure of the microchip 1 will be described in more detail.

In FIG. 9, the reference numeral 117 denotes a narrowing portionprovided in the flow path 11. The narrowing portion 117 is formed suchthat the vertical cross-sectional area with respect to the fluid feedingdirection gradually becomes smaller from the upstream side to thedownstream side in the flow path.

FIG. 11 are schematic cross-sectional diagrams for explaining thesetting position of the minute pipe 116, the structure of the flow path11 in the vicinity of the narrowing portion 117, and states of theflowing sample fluid laminar flow and sheath fluid laminar flow. FIG.11(A) shows a horizontal cross-sectional diagram (XY cross-sectionaldiagram), and FIG. 11(B) shows a vertical cross-sectional diagram (ZXcross-sectional diagram). In the figures, the symbol S decodes thesample fluid laminar flow, the symbol T decodes the sheath fluid laminarflow, and the symbol P decodes minute particles included in the samplefluid.

The sample fluid laminar flow S is introduced into the sheath fluidlaminar flow T flowing through the flow path 11 via the minute pipe 116and fed while surrounded by the sheath fluid laminar flow T (3D laminarflow) as shown in the figures.

A flow path side wall of the narrowing portion 117 is formed to narrowin the fluid feeding direction along the Y-axis direction in the figure,and the narrowing portion 117 is of a cone shape that gradually narrowsin an upper view. By this shape, the narrowing portion 117 narrows alaminar flow width of the sheath fluid and the sample fluid and feedsthem. Moreover, the narrowing portion 117 is formed to be an inclinedsurface whose flow path bottom surface becomes higher in a depthdirection (Z-axis direction) from the upstream side to the downstreamside and also narrows the laminar flow width in the same direction.

As described above, by forming the 3D laminar flow in which the samplefluid laminar flow S is surrounded by the sheath fluid laminar flow Tand narrowing the laminar flow width of the 3D laminar flow to feed it,the minute particles P can be arranged one by one in the narrowed samplefluid laminar flow S. As a result, a flow sending position of the minuteparticles P in the flow path 11 can be positioned, and laser light fromthe detection means 31 can be accurately irradiated onto the minuteparticles P in the detection portion F.

In particular, since the laminar flow width of the sample fluid laminarflow S can be narrowed in not only the horizontal direction of themicrochip 1 (Y-axis direction in FIG. 11(A)) but also the verticaldirection (Z-axis direction in FIG. 11(B)) by the narrowing portion 117,a focal position of the laser light in the depth direction of the flowpath 11 can be made to accurately match the flow sending position of theminute particles P. Therefore, it becomes possible to obtain a highmeasurement sensitivity by accurately irradiating laser light onto theminute particles P.

Here, it is considered that, by forming the flow path 11 as asufficiently-thin flow path and introducing the sample fluid laminarflow S into the sheath fluid laminar flow T flowing through the flowpath 11 using the minute pipe 116 having a small diameter, it ispossible to form a 3D laminar flow in which the laminar flow width isnarrowed in advance. In this case, however, by making the diameter ofthe minute pipe 116 small, there is a possibility that the minuteparticles P might get stuck in the minute pipe 116.

By providing the narrowing portion 117 in the microchip 1, it ispossible to narrow down the laminar flow width after the 3D laminar flowis formed using the minute pipe 116 having a sufficiently-largerdiameter than the diameter of the minute particles P included in thesample fluid. Therefore, the problem of the minute pipe 116 gettingstuck is not caused.

FIG. 11 have shown the case where the minute pipe 116 is provided suchthat the center thereof becomes coaxial with the center of the flow path11. In this case, the sample fluid laminar flow S is introduced into thecenter of the sheath fluid laminar flow T flowing through the flow path11. The position of the sample fluid laminar flow S in the sheath fluidlaminar flow T can be set arbitrarily by adjusting the opening positionof the minute pipe 116 in the flow path 11. Moreover, for narrowing downthe laminar flow width, the narrowing portion 117 only needs to beformed such that the area of the vertical cross section with respect tothe fluid feeding direction gradually decreases from the upstream sideto the downstream side in the flow path. Without being limited to theshape shown in FIG. 11, the narrowing portion 117 can be formed suchthat, for example, both the flow path bottom surface and upper surfaceare formed as inclined surfaces so that narrowing down can be performed.

The inner diameter of the minute pipe 116 can be set as appropriatebased on the diameter of the minute particles P. For example, whencarrying out a reaction analysis with blood cells using blood as thesample fluid, the inner diameter of the minute pipe 116 is favorablyabout 10 to 500 μm. Further, the width and depth of the flow path 11 atthe opening position of the minute pipe 116 only need to be set asappropriate based on the outer diameter of the minute pipe 116 ontowhich the diameter of the minute particles P is reflected. For example,when the inner diameter of the minute pipe 116 is about 10 to 500 μm,the width and depth of the flow path 11 at the opening position of theminute pipe 116 are favorably about 100 to 2000 μm. It should be notedthat the cross-sectional shape of the minute pipe may be an arbitraryshape such as an oval, a square, and a triangle instead of a circle.

The laminar flow width of the sample fluid laminar flow S and the sheathfluid laminar flow T that has been narrowed down by the narrowingportion 117 can re narrowed down to an arbitrary laminar flow width byappropriately adjusting the vertical cross-sectional area of thenarrowing portion 117 with respect to the fluid feeding direction. Forexample, when a flow path length of the narrowing portion 17 isrepresented by 1 and an inclination angle of the flow path bottomsurface is represented by δ₃ in FIG. 11(B), the narrowing width of the3D laminar flow at the narrowing portion 17 becomes 1*tan δ₃. Therefore,by adjusting the flow path length l and the inclination angle δ₃ asappropriate, an arbitrary narrowing width can be set. Furthermore, withnarrowing angles of the flow path. side wall of the narrowing portion117 in the Y-axis direction being represented by δ₁ and δ₂ whichsatisfy, together with δ₃, “δ₃=2*δ₁, δ₁=δ₂” in FIG. 11(A), the samplefluid laminar flow S and the sheath fluid laminar flow T can becontracted isotropically, and the laminar flow width can be narroweddown without disturbing the 3D laminar flow formed by the minute pipe116.

The laminar flow width of the sample fluid. laminar flow S and thesheath fluid laminar flow T at the detection portion F, that has beennarrowed by the narrowing portion 117, is favorably about 20 to 2000 μmin width and depth of the flow path 11.

In FIG. 9, the reference numeral 118 denotes a pressor portion that isprovided in the flow path 11 at a position upstream from the orifice 111and downstream from the detection portion F. The pressor portion 118 isformed such that the vertical cross-sectional area with respect to thefluid feeding direction gradually decreases from the upstream side tothe downstream side in the flow path. In other words, similar to thenarrowing portion 117, the pressor portion 118 is formed such that theflow path side wall narrows in the Y-axis direction in the figure alongthe fluid feeding direction and the flow path bottom surface becomes aninclined surface that becomes higher in the depth direction (Z-axisdirection) from the upstream side to the downstream side.

FIG. 12 are schematic cross-sectional diagrams for explaining thestructures of the pressor portion 118 and the flow path 11 in thevicinity of the orifice 111, and the states of the flowing sample fluidlaminar flow and sheath fluid laminar flow. FIG. 12(A) shows ahorizontal cross-sectional diagram (XY cross-sectional diagram), andFIG. 12(B) shows a vertical cross-sectional diagram (ZX cross-sectionaldiagram). In the figures, the symbol S decodes the sample fluid laminarflow, the symbol T decodes the sheath fluid. laminar flow, and thesymbol P decodes minute particles included in the sample fluid.

The sample fluid laminar flow S and the sheath fluid laminar flow T arefed while the laminar flow width is narrowed down by the pressor portion118 in the Y- and Z-axis directions in the figure. By the narrowing ofthe laminar flow width, the pressor portion 118 functions to increase afluid feeding pressure of the sample fluid and the sheath fluid in theflow path 11 and discharging the fluids from the orifice 111 at a highpressure.

The laminar flow width of the sample fluid laminar flow S and the sheathfluid laminar flow T at the orifice 111 part can be narrowed down to anarbitrary laminar flow width by appropriately adjusting the verticalcross-sectional area of the pressor portion 118 with respect to thefluid feeding direction. For example, when the flow path length of thepressor portion 118 is represented by 1 and the inclination angle of theflow path bottom surface is represented by δ₃ in FIG. 12(B), thenarrowing width of the 3D laminar flow at the pressor portion 118becomes 1*tan δ₃. Therefore, an arbitrary narrowing width can be set byadjusting the flow path length l and the inclination angle δ₃ asappropriate. The laminar flow width of the sample fluid laminar flow Sand the sheath. fluid laminar flow T at the orifice 111 part isfavorably about 20 to 500 μm in width and depth of the orifice 111 part.

It should be noted that the pressor portion 118 is the same as thenarrowing portion 117 in the point that the narrowing of the laminarflow width of the sample fluid laminar flow S and the sheath fluidlaminar flow T can be carried out with both the flow path bottom surfaceand upper surface of the pressor portion 118 as inclined surfaces andthe shape of the pressor portion 118 is not limited to the shape shownin the figures. Furthermore, with narrowing angles of the flow path sidewall of the pressor portion 118 in the Y-axis direction beingrepresented by δ₁ and δ₂ which satisfy, together with the narrowingangle δ₃ in the Z-axis direction, “δ₃=2*δ₁, δ₁=δ₂” in FIG. 12(A), the 3Dlaminar flow formed by the minute pipe 116 can be contractedisotropically, and the laminar flow width can be narrowed down withoutdisturbing the 3D laminar flow as described above with respect to thenarrowing portion 117.

Similar to the pressor portion 118 of the flow path 11, pressor portions128 and 138 are provided in the flow paths 12 and 13 for dischargingfluids from the orifices 121 and 131 at a high pressure. The flow pathwidth and depth at the orifice 121, 131 parts can be narrowed down to anarbitrary system by appropriately adjusting the vertical cross-sectionalareas of the pressor portions 128 and 138 with respect to the fluidfeeding direction. By adjusting the diameters of the orifices 121 and131 and the like, it is possible to adjust sizes of the droplets B and Cand adjust the amount of substances to be mixed with the droplet A.

FIG. 13 are schematic cross-sectional diagrams for explaining the widthsand depths at respective parts of the flow path 11. The figures eachshow a YZ cross section of the flow path 11. FIG. 13(A) shows a crosssection of the opening position of the minute pipe 116, FIG. 13(B) showsa cross section of the detection portion F, and FIG. 13(C) shows a crosssection of the orifice 111 part of the flow path 11.

As shown in FIG. 13(A), at the opening position of the minute pipe 116,the sample fluid laminar flow S and the sheath fluid laminar flow T arefed as the 3D laminar flow in which the sample fluid laminar flow S issurrounded by the sheath fluid laminar flow T. As already describedabove, the width and depth of the flow path 11 at the opening positionof the minute pipe 116 are set as appropriate to, for example, about 100to 2000 μm based on the outer diameter of the minute pipe 116 onto whichthe diameter of the minute particles P is reflected.

The 3D laminar flow formed by the minute pipe 116 is fed to thedetection portion F in a state where the laminar flow width is narroweddown by the narrowing portion 117 (see FIG. 13(B)). By narrowing downthe laminar flow width by the narrowing portion 117, the minuteparticles P are arranged one by one in the sample fluid laminar flow Sto be fed to the detection portion F.

The laminar flow width of the sample fluid laminar flow S and the sheathfluid laminar flow T at the detection portion F can be set asappropriate by appropriately adjusting the vertical cross-sectional areaof the narrowing portion 117 with respect to the fluid feedingdirection. The width (W) and depth (H) of the flow path 11 at thedetection portion F are set to be about 20 to 2000 μm for making anoptical detection angle (numerical aperture of optical system) of thedetection means 31 sufficiently large. As a result, an optical detectionangle γ and the numerical aperture can be made sufficiently large.

Furthermore, the shape of the flow path 11 at the light irradiationportion 33 is favorably a rectangle with respect to an irradiationdirection of measurement light irradiated by a light detection means 3with an increased width (W) with respect to the depth (H). With such abroad shape of the flow path 11 at the light irradiation portion 33, itis possible to increase the numerical aperture of the optical system.

The sample fluid laminar flow S and the sheath fluid laminar flow T thathave passed the detection portion F are fed to the orifice 111 after thelaminar flow width is again narrowed down by the pressor portion 118 asshown in FIG. 13(C). By narrowing down the laminar flow width by thepressor portion 118, a discharge pressure of the sample fluid and sheathfluid from the orifice 111 can be increased.

The laminar flow width of the sample fluid laminar flow S and the sheathfluid laminar flow T at the orifice 111 part can be set arbitrarily byappropriately adjusting the vertical cross-sectional area of the pressorportion 118 with respect to the fluid feeding direction. For forminghigh-frequency droplets at a high speed at the orifice 111, it isfavorable to make the laminar flow width of the sample fluid laminarflow S and the sheath fluid laminar flow T at the orifice 111 part smallto thus sufficiently increase the discharge pressure of the sample fluidand the sheath fluid. Therefore, the width (w) and depth (h) of the flowpath 11 at the opening of the orifice 111 are favorably set to be about20 to 500 μm.

Here, the case where the laminar flow width. of the 3D laminar flowformed by the minute pipe 116 is first made a width suited for detectingminute particles in the detection portion F by the narrowing portion 117and is then made a width with which high-frequency droplets can beformed by the pressor portion 113 has been described. The narrowing ofthe laminar flow width in the flow path 11 does not need to be carriedout in two steps of the narrowing portion 117 and the pressor portion118 and can be carried out such that the flow path. width and depthgradually and consecutively decrease from the opening position of theminute pipe 116 of the flow path 11 to the orifice 111 as shown in FIG.14, for example.

In addition, the flow path 11 may take various shapes as long as theflow path width and depth at the opening position of the minute pipe116, the detection portion F, and the orifice 111 part are within arange of the favorable numerical values.

Further, the shape of the opening of the orifice 111 may be an arbitraryshape such as a square, a rectangle, and a circle. Furthermore, as shownin FIG. 14, an end surface part of the opening portion may be formed inan inverse tapered shape. With such a trumpet shape of the end surfacepart of the opening of the orifice 111, drain of the formed droplets canbe improved.

(4-3) Dispense by Charge Means

In the microchip 1, the minute pipe 116 is formed of metal to which avoltage can be applied and structured as a charge means for imparting apositive or negative charge to the sheath fluid and sample fluid flowingthrough the flow path 11. By applying a voltage to the sheath fluid andsample fluid by applying a voltage to the minute pipe 116 whendischarging droplets of the sample fluid and sheath fluid flowingthrough the flow path 11 from the orifice 111, a positive or negativecharge can be imparted to the discharged droplets.

By imparting a positive or negative charge to the droplets A dischargedfrom the orifice 111 by the minute pipe 116, a positive or negativecharge can be imparted to the droplets G obtained after the collisionwith the droplets B and C. Accordingly, the movement direction of thedroplet G can be controlled by the electric repulsion force orabsorption force that acts between the first paired electrodes 51, 51and the second paired electrodes 52, 52 (see FIG. 8).

The flying direction of the droplet G after passing the second pairedelectrodes 52, 52 can be controlled arbitrarily in the X- and Y-axisdirections in the figures by varying the voltage applied to the firstpaired electrodes 51, 51 and the second paired electrodes 52, 52 andadjusting the intensity of the electric action force between the dropletG.

Accordingly, the droplet G can be guided to each of the plurality ofareas 21 formed in the vessel 2 and retrieved in the areas. It should benoted that the control of the flying direction of the droplet G can beadjusted by varying a voltage applied to the minute pipe 116.

(4-4) Dispense by Drive Means

FIG. 15 is a schematic diagram for explaining another structure fordispensing the droplet G obtained after the collision and mixing in themicrochip-type substance mixing apparatus. The figure shows a structurefor dispensing the droplet G to the plurality of areas 21 of the vessel2 while moving the microchip 1 by a drive means.

Here, descriptions will be given on an example where the droplet G isdispensed using the microchip 1 on which a plurality of structural unitsconstituted of the flow paths 11, 12, and 13 etc. for forming thedroplet G are provided with respect to 96 wells (areas 21) formed in amulti-plate (vessel 2) (hereinafter, simply referred to as “structuralunit”).

In the vessel 2, 8 areas 21 are arranged in the X-axis direction, and 12areas 21 are arranged in the Y-axis direction in the figure.Accordingly, also on the microchip 1 shown in the figure, 8 structuralunits are arranged in one row in the X-axis direction. The arrangementinterval of the structural units coincides with the interval of theareas 21 in the X-axis direction. As a result, the mixed droplets Gdischarged from the structural units are retrieved in the areas 21arranged in a row.

The microchip 1 is movable by a drive means (not shown). By sequentiallymoving the relative position of the microchip 1 with respect to thevessel 2 by the drive means, 0 or 1 or more droplet P can be retrievedin each of the plurality of areas 21 formed in the vessel 2.Specifically, while sequentially moving the microchip 1 in the Y-axisdirection, the droplets G are dispensed to 8 areas 21 arranged in theX-axis direction every time. As described above, by forming theplurality of structural units on the microchip 1 and dispensing themixed droplets thereto, mixing of a large number of reaction systems canbe carried out in a short time.

INDUSTRIAL APPLICABILITY

In the substance mixing apparatus according to the present invention, bydischarging fluids including substances to be mixed as droplets from theorifices of the flow paths and causing them to collide with one another,the substances included in the fluids can be mixed uniformly in a shorttime. Moreover, since the substances can be incorporated into thedroplets in certain amounts, variances in the amount of substances to bemixed are not caused. Therefore, the substance mixing apparatusaccording to the present invention is useful for carrying out ahigh-speed and large-scale reaction of various compounds and may be usedfor various reactions and analyses such as a polymerase chain reaction(PCR) and a mass analysis.

Furthermore, in the substance mixing apparatus according to the presentinvention, the fluid including minute particles is discharged asdroplets from the orifice of the flow path, the fluid including asubstance to be mixed is discharged as droplets from the orifice of theother flow path, and the droplets are caused to collide with oneanother. As a result, the minute particles and substance included in thedroplets can be mixed uniformly in a short time. Therefore, it isparticularly useful for mixing minute particles includingbiologically-relevant minute particles such as a cell, a microorganism,and a liposome and synthetic particles such as latex particles, gelparticles, and industrial particles with various compounds, and carryingout a high-speed and large-scale analysis on a reaction of the minuteparticles and compounds.

DESCRIPTION OF SYMBOLS

-   A, B, C, G, H droplet-   F detection portion-   P minute particle-   S sample fluid laminar flow-   T sheath fluid laminar flow-   1 microchip-   11, 12, 13 flow path-   111, 121, 131 orifice-   112, 122, 132 oscillation device-   113, 123 charge means-   114 sheath fluid inlet-   115 sample fluid inlet-   116 minute pipe-   117 narrowing portion-   118, 128, 138 pressor portion-   124, 134 inlet-   51, 52 paired electrode-   2 vessel-   21 area-   31, 32, 33 detection means-   4 control means

The invention claimed is:
 1. A microchip, comprising: at least one flowpath; a sheath fluid inlet configured to introduce a sheath fluid intothe at least one flow path; and a sample fluid inlet configured tointroduce a sample fluid into the sheath fluid in the at least one flowpath, wherein the sample fluid includes a plurality of minute particles,the at least one flow path comprises: an orifice configured toexternally discharge the sheath fluid and the sample fluid that flowthrough the at least one flow path, wherein an opening of the orificehas a rectangular shape, and an end surface part of the orifice has aninverse tapered shape; a detection portion in which light generated fromthe plurality of minute particles is detected, wherein the detectionportion is downstream of the sample fluid inlet and upstream of theorifice; a first narrowing portion downstream of the sample fluid inletand upstream of the detection portion, wherein at least onecross-sectional area of the first narrowing portion is larger than across-sectional area of the detection portion, the at least onecross-sectional area of the first narrowing portion is gradually smallerfrom an upstream side of the first narrowing portion to a downstreamside of the first narrowing portion, and the first narrowing portion isin a substrate layer; and a second narrowing portion downstream of thedetection portion and upstream of the orifice, wherein at least onecross-sectional area of the second narrowing portion is smaller than thecross-sectional area of the detection portion, and the at least onecross-sectional area of the second narrowing portion is graduallysmaller from an upstream side of the second narrowing portion to adownstream side of the second narrowing portion, and the microchip isoscillated at a specific oscillation frequency to discharge droplets ofthe sheath fluid and the sample fluid from the orifice.
 2. The microchipaccording to claim 1, wherein the sample fluid is introduced into acenter of the sheath fluid in the at least one flow path such that thesample fluid is surrounded by the sheath fluid.
 3. The microchipaccording to claim 2, further comprising at least two sheath fluid flowpaths connected with the sheath fluid inlet, wherein the at least twosheath fluid flow paths are connected at a position where the samplefluid is present.
 4. The microchip according to claim 1, wherein thefirst narrowing portion comprises a bottom surface, and the bottomsurface becomes higher in a depth direction from the upstream side ofthe first narrowing portion to the downstream side of the firstnarrowing portion.
 5. The microchip according to claim 1, wherein thefirst narrowing portion comprises an upper surface, and the uppersurface becomes lower in a depth direction from the upstream side of thefirst narrowing portion to the downstream side of the first narrowingportion.
 6. The microchip according to claim 1, wherein the firstnarrowing portion comprises a side wall, and the side wall graduallynarrows in a direction vertical to a fluid flow direction from theupstream side of the first narrowing portion to the downstream side ofthe first narrowing portion.
 7. The microchip according to claim 1,further comprising a minute pipe connected with the sample fluid inlet,wherein the minute pipe is configured to introduce the sample fluid intothe at least one flow path.
 8. The microchip according to claim 7,wherein the minute pipe comprises a metal, and the minute pipe isconfigured to be applied with a voltage.
 9. The microchip according toclaim 1, further comprising a plurality of flow paths including the atleast one flow path.
 10. The microchip according to claim 1, wherein themicrochip is in two substrate layers, and the two substrate layersincludes the substrate layer.
 11. The microchip according to claim 1,wherein an inclination angle of a left side wall of the first narrowingportion with a specific direction is same as an inclination angle of aright side wall of the first narrowing portion with the specificdirection.
 12. An analysis apparatus, comprising: a microchip thatcomprises: at least one flow path; a sheath fluid inlet configured tointroduce a sheath fluid into the at least one flow path; and a samplefluid inlet configured to introduce a sample fluid into the sheath fluidin the at least one flow path, wherein the sample fluid includes aplurality of minute particles, and the at least one flow path comprises:an orifice configured to externally discharge the sheath fluid and thesample fluid that flow through the at least one flow path, wherein anopening of the orifice has a rectangular shape, and an end surface partof the orifice has an inverse tapered shape; a detection portiondownstream of the sample fluid inlet and upstream of the orifice; afirst narrowing portion downstream of the sample fluid inlet andupstream of the detection portion, wherein a cross-sectional area of thefirst narrowing portion is gradually smaller from an upstream side ofthe first narrowing portion to a downstream side of the first narrowingportion, the first narrowing portion is in a substrate layer, and across-sectional area of the detection portion is smaller than across-sectional area of a position where the sample fluid is introduced;and a second narrowing portion downstream of the detection portion andupstream of the orifice, wherein the cross-sectional area of thedetection portion is larger than at least one cross-sectional area ofthe second narrowing portion, and the at least one cross-sectional areaof the second narrowing portion is gradually smaller from an upstreamside of the second narrowing portion to a downstream side of the secondnarrowing portion; a detector configured to detect, through thedetection portion, light generated from the plurality of minuteparticles; and an oscillation device configured to: contact themicrochip; and oscillate the microchip at a specific oscillationfrequency such that droplets of the sheath fluid and the sample fluidare discharged from the orifice.
 13. The analysis apparatus according toclaim 12, wherein the oscillation device is further configured tooscillate the microchip such that the droplets collide with one another.14. The analysis apparatus according to claim 12, further comprising acontroller configured to: calculate a flow sending interval of theplurality of minute particles based on a detection signal of theplurality of minute particles from the detector; and control thespecific oscillation frequency of the oscillation device based on theflow sending interval.
 15. The analysis apparatus according to claim 14,wherein the controller is further configured to control the specificoscillation frequency such that a specific number of the plurality ofminute particles are present in each of the droplets discharged from theorifice.
 16. The analysis apparatus according to claim 12, furthercomprising: at least one charge unit configured to impart a charge tothe droplets discharged from the orifice; and a first electrode and asecond electrode that are along a movement direction of the droplets,wherein the second electrode is opposite to the first electrode.
 17. Theanalysis apparatus according to claim 16, wherein the first electrodeand the second electrode are configured to: generate an electric actionforce by the charge imparted to the droplets; and control the movementdirection of the droplets by the electric action force.
 18. The analysisapparatus according to claim 12, wherein the microchip further comprisesa plurality of flow paths including the at least one flow path.
 19. Theanalysis apparatus according to claim 12, further comprising a minutepipe configured to: connect with the sample fluid inlet; and introducethe sample fluid into the at least one flow path.
 20. The analysisapparatus according to claim 19, wherein the minute pipe comprises ametal, and the minute pipe is configured to be applied with a voltage.